Device for detecting an analyte

ABSTRACT

This invention relates to a device for detecting an analyte in a sample comprising: a radiation source adapted to generate a series of pulses of electromagnetic radiation; a transducer having a pyroelectric or piezoelectric element and electrodes which is capable of transducing energy generated by non-radiative decay into an electrical signal; a detector which is capable of detecting the electrical signal generated by the transducer; a first reagent proximal to the transducer, the first reagent having a binding site which is capable of binding a labelled reagent proportionally to the concentration of the analyte in the sample, which labelled reagent being capable of absorbing the electromagnetic radiation generated by the radiation source to generate energy by non-radiative decay; a second reagent proximal to the transducer, the second reagent having a lower affinity for the labelled reagent under the conditions of the assay than the first reagent; and a third reagent proximal to the transducer, the third reagent having a binding site which is capable of binding the labelled reagent, wherein the third reagent has an affinity for the labelled reagent which is less influenced than the first reagent by the concentration of the analyte or the complex or derivative of the analyte.

This application is a divisional of U.S. patent application Ser. No. 14/110,033, filed on Dec. 16, 2013, which is a National Phase of International Application No. PCT/GB2012/050772, filed Apr. 5, 2012, which claims priority to U.S. Provisional Patent Application No. 61/472,886, filed on Apr. 7, 2011 and United Kingdom Patent Application No. 1105828.6, filed Apr. 6, 2011, all of which are incorporated herein by reference in their entireties.

The present invention relates to a device for detecting an analyte, and particularly to improving accuracy and precision in a device incorporating a piezo/pyroelectric transducer.

The monitoring of analytes in solution, such as biologically important compounds in bioassays, has a broad applicability. Accordingly, a wide variety of analytical and diagnostic devices are available.

WO 90/13017 discloses a pyroelectric or other thermoelectric transducer element in a strip form. Thin film electrodes are provided and one or more reagents are deposited on the transducer surface. The reagent undergoes a selective colorimetric change when it comes into contact with the species being detected. The device is then typically inserted into a detector where the transducer is illuminated usually through the transducer by an LED light source and light absorption by the reagent is detected as microscopic heating at the transducer surface. The electrical signal output from the transducer is processed to derive the concentration of the species being detected.

WO 2004/090512 discloses a device based on the technology disclosed in WO 90/13017, but relies on the finding that energy generated by non-radiative decay in a substance on irradiation with electromagnetic radiation may be detected by a transducer even when the substance is not in contact with the transducer, and that the time delay between the irradiation with electromagnetic radiation and the electrical signal produced by the transducer is a function of the distance of the substance from the surface of the film. This finding provided a device capable of “depth profiling” which allows the device to distinguish between an analyte bound to the surface of the transducer and an analyte in the bulk liquid. This application therefore discloses a device which is able to be used in assays, typically bioassays, without having to carry out a separate washing step between carrying out a binding event and detecting the results of that event (termed a “homogeneous” assay).

The system described in WO 90/13017 and WO 2004/090512 uses a piezo/pyroelectric transducer to measure binding events. The binding events take place at the surface of the transducer, and the measurement process is initiated by pulsing electromagnetic radiation (light) into the system. Light absorption causes localised heating of a labelled reagent which, in turn generates an electric charge in the transducer. The electrical output can be interrogated in such a fashion as to distinguish between the bound and unbound reagent, and hence characterise the amount of analyte in a fluid sample. The rate of binding to the surface in situ can be determined without separation steps.

Any measurement process will suffer from imprecision or inaccuracy in the measurement owing to natural variations in the components which make up the system. There may also be interference in the measurement process from environmental factors, such as temperature or humidity. Measurements which are carried out in bodily fluids, such as blood or plasma, may also be affected by the composition of those fluids. This may be due to interfering factors, such as lipids, bilirubin and heterophilic antibodies, or due to natural variations in viscosity, hematocrit, etc.

It is common in laboratory analysers to run calibrations at regular intervals, which confirm that the instrument is performing appropriately, and also to calibrate the instrument. This calibration process improves the measurement process by adjusting the system for variability in the components from different batches.

However, in the system described in WO 90/13017 and WO 2004/090512, the kinetic binding of a labelled reagent to the sensor surface is monitored in situ by monitoring the rate of change of signal over time in the presence of the analyte (or a complex or derivative of the analyte) to be measured. This is different to other immunoassay systems which often measure some form of equilibrium position that has been achieved after an incubation period of a pre-determined length. In addition, since the system described in WO 90/13017 and WO 2004/090512 can measure the labelled reagent relative to the sensor surface, unwanted movement of the labelled reagent, or indeed other particles in the measurement chamber, can interfere with the signal measurement. There, therefore, remains a need for systems providing improved accuracy and precision.

Accordingly, the present invention provides a device for detecting an analyte in a sample comprising:

a radiation source adapted to generate a series of pulses of electromagnetic radiation; a transducer having a pyroelectric or piezoelectric element and electrodes which is capable of transducing energy generated by non-radiative decay into an electrical signal; a detector which is capable of detecting the electrical signal generated by the transducer; a first reagent proximal to the transducer, the first reagent having a binding site which is capable of binding a labelled reagent proportionally to the concentration of the analyte in the sample, which labelled reagent being capable of absorbing the electromagnetic radiation generated by the radiation source to generate energy by non-radiative decay; a second reagent proximal to the transducer, the second reagent having a lower affinity for the labelled reagent under the conditions of the assay than the first reagent; and a third reagent proximal to the transducer, the third reagent having a binding site which is capable of binding the labelled reagent, wherein the third reagent has an affinity for the labelled reagent which is less influenced than the first reagent by the concentration of the analyte or the complex or derivative of the analyte.

Thus, the present invention provides a device for detecting an analyte which incorporates both positive (third reagent) and negative (second reagent) controls to improve the accuracy and precision in the detection (via the first reagent).

The present invention will now be described with reference to the drawings, in which:

FIG. 1 shows a schematic representation of the chemical sensing device of WO 2004/090512 which is used with the present invention;

FIG. 2 shows a sandwich immunoassay using the device of the present invention;

FIG. 3 shows a cartridge according to the present invention;

FIG. 4 shows kinetic output in a TSH assay;

FIG. 5 shows a TSH dose-response curve without using controls;

FIG. 6 shows a TSH dose-response curve using positive and negative controls;

FIG. 7 shows a digoxin dose-response curve without using controls;

FIG. 8 shows a digoxin dose-response curve using positive and negative controls;

FIG. 9 shows digoxin assay dose-response curves for a cartridge with multiple dynamic ranges;

FIGS. 10-13 show a TSH assay in whole blood using no control, negative control only, positive control only and both controls, respectively; and

FIG. 14 shows instrument outputs for simultaneous determination of TSH and digoxin levels using the same controls for each assay.

The device of the present invention is used for detecting an analyte in a sample (which may be via the detection of a complex or derivative of the analyte). The device comprises: a radiation source adapted to generate a series of pulses of electromagnetic radiation; a transducer having a pyroelectric or piezoelectric element and electrodes which is capable of transducing energy generated by non-radiative decay into an electrical signal; and a detector which is capable of detecting the electrical signal generated by the transducer. In a preferred embodiment, the device of the present invention is based on the device described in WO 2004/090512.

FIG. 1 shows a chemical sensing device 1 for use in accordance with the present invention which relies on heat generation in a label 2 on irradiation of the label 2 with electromagnetic radiation. For the sake of simplicity, only the label is shown in FIG. 1 (the remaining components of the device of the present invention will be described in further detail hereinbelow). FIG. 1 shows the chemical sensing device 1 in the presence of a label 2. The device 1 comprises a pyroelectric or piezoelectric transducer 3 having electrode coatings 4,5. The transducer 3 is preferably a poled polyvinylidene fluoride film. The electrode coatings 4,5 are preferably transparent and most preferably formed from indium tin oxide. The electrodes preferably have a thickness of about 35 nm, although almost any thickness is possible from a lower limit of 1 nm below which the electrical conductivity is too low and an upper limit of 100 nm above which the optical transmission is too low (it should not be less than 80% T). In a particularly preferred embodiment, the transducer is an indium tin oxide-coated polyvinylidene fluoride film.

The label 2 is held proximal to the transducer 3 by a binding event. A preferred feature of the present invention is that the label 2 generates heat when irradiated by a source of electromagnetic radiation (typically termed “light”) 6, preferably visible light. The light source may be, for example, an LED. The light source 6 illuminates the label 2 with light of the appropriate wavelength (e.g. a complementary colour). Although not wishing to be bound by theory, it is believed that the label 2 absorbs the light to generate an excited state which then undergoes non-radiative decay thereby generating energy, indicated by the curved lines in FIG. 1. This energy is primarily in the form of heat (i.e. thermal motion in the environment) although other forms of energy, e.g. a shock wave, may also be generated. The energy is, however, detected by the transducer and converted into an electrical signal. The device of the present invention is calibrated for the particular label being measured and hence the precise form of the energy generated by the non-radiative decay does not need to be determined. Unless otherwise specified the term “heat” is used herein to mean the energy generated by non-radiative decay. The light source 6 is positioned so as to illuminate the label 2. Preferably, the light source 6 is positioned opposite the transducer 3 and electrodes 4,5 and the label 2 is illuminated through the transducer 3 and electrodes 4,5. The light source may be an internal light source within the transducer in which the light source is a guided wave system. The wave guide may be the transducer itself or the wave guide may be an additional layer attached to the transducer. The wavelength of illumination depends on the label used; for example, for 40 nm gold labels the preferred wavelength is 525 nm and for carbon labels the preferred wavelength is 690 nm.

The energy generated by the label 2 is detected by the transducer 3 and converted into an electrical signal. The electrical signal is detected by a detector 7. The light source 6 and the detector 7 are both under the control of the controller 8. The light source 6 generates a series of pulses of light (the term “light” used herein means any form of electromagnetic radiation unless a specific wavelength is mentioned) which is termed “chopped light”. In principle, a single flash of light, i.e. one pulse of electromagnetic radiation, would suffice to generate a signal from the transducer 3. However, in order to obtain a reproducible signal, a plurality of flashes of light are used which in practice requires chopped light. The frequency at which the pulses of electromagnetic radiation are applied may be varied. At the lower limit, the time delay between the pulses must be sufficient for the time delay between each pulse and the generation of an electrical signal to be determined. At the upper limit, the time delay between each pulse must not be so large that the period taken to record the data becomes unreasonably extended. Preferably, the frequency of the pulses is from 1-50 Hz, more preferably 1-10 Hz and most preferably 2 Hz. This corresponds to a time delay between pulses of 20-1,000 ms, 100-1,000 ms and 500 ms, respectively. In addition, the so-called “mark-space” ratio, i.e. the ratio of on signal to off signal is preferably one although other ratios may be used without deleterious effect. There are some benefits to using a shorter on pulse with a longer off signal, in order to allow the system to approach thermal equilibrium before the next pulse perturbs the system. In one embodiment, a light pulse of 1-50 ms, preferably 8 ms, followed by a relaxation time of 10-500 ms, preferably 100 ms allows a more precise measurement of particles bound directly to the surface. Sources of electromagnetic radiation which produce chopped light with different frequencies of chopping or different mark-space ratios are known in the art. The detector 7 determines the time delay between each pulse of light from light source 6 and the corresponding electrical signal detected by detector 7 from transducer 3. The applicant has found that this time delay is a function of the distance, d. The signal is preferably measured from 2-7 ms.

Any method for determining the time delay between each pulse of light and the corresponding electrical signal which provides reproducible results may be used. Preferably, the time delay is measured from the start of each pulse of light to the point at which a maximum in the electrical signal corresponding to the absorption of heat from bound label is detected as by detector 7.

The finding that the label 2 may be separated from the transducer surface and that a signal may still be detected was surprising since the skilled person would have expected the heat to be dispersed into the surrounding medium and hence be undetectable by the transducer 3 or at least for no meaningful signal to be received by the transducer. It was found, surprisingly, that not only was the signal detectable through an intervening medium capable of transmitting energy to the transducer 3, but that different distances, d, may be distinguished (this has been termed “depth profiling”) and that the intensity of the signal received is proportional to the concentration of the label 2 at the particular distance, d, from the surface of the transducer 3. Moreover, it was found that the nature of the medium itself influences the time delay and the magnitude of the signal at a given time delay.

The device of the present invention has particular applicability in performing immunoassays.

In a typical immunoassay, an antibody specific for an antigen of interest is attached to a polymeric support such as a sheet of polyvinylchloride or polystyrene. A drop of cell extract or a sample of serum or urine is laid on the sheet, which is washed after formation of the antibody-antigen complex. Antibody specific for a different site on the antigen is then added, and the sheet is again washed. This second antibody carries a label so that it can be detected with high sensitivity. The amount of second antibody bound to the sheet is proportional to the quantity of antigen in the sample. This assay and other variations on this type of assay are well known, see, for example, “The Immunoassay Handbook, 2nd Ed.” David Wild, Ed., Nature Publishing Group, 2001. The device of the present invention may be used in any of these assays. Sandwich, competitive, displacement and anti-complex antibody immunoassays also warrant particular mention.

By way of an explanation of the principle underlying the present invention, FIG. 2 shows a typical capture antibody assay using the device of the present invention (although only the first reagent is shown). The device includes a transducer 3 and a sample chamber 9 for holding a liquid 10 containing an analyte 11 dissolved or suspended therein. The transducer 3 has a first reagent, i.e. antibody 12, attached thereto. The first reagent 12 is shown attached to the film in FIG. 2 and this attachment may be via a covalent bond or by non-covalent adsorption onto the surface, such as by hydrogen bonding. Although the first reagent is shown as attached to the transducer, any technique for holding the first reagent 12 proximal to the transducer 3 is applicable. For example, an additional layer may separate the first reagent 12 and the transducer 3, such as a parylene polymer layer, or the antibody could be attached to inert particles and the inert particles are then attached to the transducer 3. Alternatively, the first reagent 12 could be entrapped within a gel layer which is coated onto the surface of the transducer 3.

In use, the sample chamber is filled with liquid 10 (or any fluid) containing an analyte 11. The analyte 11 then binds to first reagent 12. Additional labelled reagent 13 is present in the liquid and a so-called “sandwich” complex is formed between the bound first reagent 12, the analyte 11 and the labelled reagent 13. An excess of labelled reagent 13 is included so that all of the bound antigen 11 forms a sandwich complex. The sample therefore contains bound labelled reagent 13 a and unbound labelled reagent 13 b free in solution.

During or following formation of the sandwich complex, the sample is irradiated using a series of pulses of electromagnetic radiation, such as light. The time delay between each pulse and the generation of an electrical signal by the transducer 3 is detected by a detector. The appropriate time delay is selected to measure primarily the heat generated by the bound labelled reagent 13 a. Since the time delay is a function of the distance of the label from the transducer 3, the bound labelled reagent 13 a may be distinguished from the unbound labelled reagent 13 b. This provides a significant advantage over the conventional sandwich immunoassay in that it removes the need for washing steps. In a conventional sandwich immunoassay, the unbound labelled reagent must be separated from the bound labelled reagent before any measurement is taken since the unbound labelled reagent interferes with the signal generated by the bound labelled reagent. However, on account of the “depth profiling” provided by the present invention, bound and unbound labelled reagent may be distinguished. Indeed, the ability to distinguish between labels proximal to the transducer (i.e. bound) and labels in the bulk solution (i.e. unbound) is a particular advantage of the present invention.

The present invention also provides a method for detecting an analyte, or a complex or derivative of the analyte, in a sample comprising the steps of exposing the sample to the device as described herein, transducing the energy generated into an electrical signal and detecting the signal. Preferably, the method is carried out without removing the sample from the transducer between the steps of exposing the sample to the transducer and transducing the energy generated into an electrical signal, i.e. the method is a homogeneous assay.

The present invention provides controls which compensate for natural variability in the components of the measuring system, variability in the samples that are measured, and variability in the environmental conditions during the measurement. This can be achieved by exposing the sample to reagents on the surface of the transducer. The different reagents are typically located at different areas of the transducer surface, these areas being coated in different reagents. These controls are defined as “negative” and “positive” controls, in the sense that the negative control should approximate the expected signal in the absence of analyte, and the positive control should approximate the expected signal when analyte has saturated the system.

To achieve detection with these controls, the device of the present invention comprises a first, second and third reagent, each of which is proximal to the transducer.

The first reagent has a binding site which is capable of binding a labelled reagent proportionally to the concentration of the analyte in the sample. The proportionality is important for the functioning of the assay since the binding must be dependent on the concentration of the analyte for any meaningful measure of the concentration of the analyte to be determined. The binding may be directly proportional or indirectly proportional to the concentration of the analyte depending on the type of assay being performed. In the case of a non-competitive assay, e.g. an immunometric assay, the binding is directly proportional to the concentration of the analyte, but for a competitive assay, the binding is indirectly proportional to the concentration of the analyte.

The first reagent may be adapted to bind to the analyte, or a complex or derivative of the analyte, in which case the labelled reagent will bind to the first reagent in the presence of the analyte, or the complex or derivative of the analyte. In this case, the first reagent has a binding site which is capable of binding to the labelled reagent in the presence of the analyte or the complex or derivative of the analyte. The binding is, however, still proportional to the concentration of the analyte.

Alternatively, the first reagent may itself be an analogue of the analyte and the labelled reagent binds directly to the first reagent (it is an analogue because it is bound to the transducer surface either through covalent bonding or non-covalent interactions). In this case, the first reagent will compete with the unbound analyte, or an unbound complex or derivative of the analyte, for the binding of the labelled reagent. Accordingly, the first reagent will simply be capable of binding to the labelled reagent.

Determining the extent of binding of the labelled reagent to the first reagent (either directly or mediated by the analyte/complex or derivative of the analyte) provides a measurement of the concentration of the analyte in the sample.

The second reagent has a lower affinity for the labelled reagent under the conditions of the assay than the first reagent. Accordingly, the second reagent provides the negative control. It is important that the affinity is considered under the conditions of the assay. The reason is that in the case of a non-competitive assay, the affinity of the first reagent for the labelled reagent is mediated by the presence of the analyte, or the complex or derivative of the analyte. Thus, in the absence of the analyte, or the complex or derivative of the analyte, neither the first nor second reagent has any affinity for the labelled reagent. However, in the presence of the analyte, or the complex or derivative of the analyte, the second reagent has a lower affinity for the labelled reagent than the first reagent.

In addition, in the embodiments where the first reagent binds to the analyte, or the complex or derivative of the analyte, the second reagent preferably has a lower affinity for the analyte or, if used, the complex or derivative of the analyte than the first reagent. The second reagent is preferably a protein and more preferably an antibody. The second reagent typically has similar chemical and physical properties to the first reagent, but provides little or no affinity for the labelled reagent under the conditions of the assay. In a particularly preferred embodiment, the second reagent has essentially no affinity for the labelled reagent under the conditions of the assay. Preferably, second reagent provides essentially no affinity for the analyte or the complex or derivative of the analyte. That is, the binding of the labelled reagent, or, where applicable, the analyte or the complex or derivative of the analyte, to the second reagent is non-specific. In this manner, the second reagent can compensate for non-specific binding of the labelled reagent to the first reagent, and can also compensate for unwanted movement of the labelled reagent relative to the transducer, e.g. by sedimentation under gravity, which can interfere with the measurement process.

The third reagent binds to the labelled reagent and has an affinity for the labelled reagent which is less influenced by the concentration in the sample of the analyte or, if used, the complex or derivative of the analyte than the first reagent and hence provides the positive control. Preferably, the third reagent has an affinity for the labelled reagent which is essentially independent of the concentration of the analyte or the complex or derivative of the analyte. More preferably, the third reagent has a higher affinity for the labelled reagent under the conditions of the assay than the first reagent. In this manner, the third reagent measures the diffusion-limited rate of binding of the labelled reagent to the transducer and hence determines the maximum signal obtainable under diffusion. At extremely high concentrations of the analyte or the complex or derivative of the analyte, concentration effects may be seen, but provided the affinity is less influenced by the concentration than that of the first reagent, the third reagent can still provide a positive control even at high concentrations.

By interrogating the output of the detector, a ratiometric signal can be obtained which defines the magnitude of the signal from binding to the first reagent (i.e. the measurement signal) relative to the binding of the second and third reagents (i.e. the negative and positive controls, respectively) as a fractional output between 0.000 and 1.000.

The first, second and third reagents may be attached to the transducer using techniques known in the art. Preferably the attachment is via non-covalent bonding, for example, a primary layer is adsorbed on to the transducer and the reagents are attached to the primary layer by a binding event.

The assay also requires the presence of a labelled reagent. By “labelled” reagent is meant a reagent which is attached to a label, which label being capable of absorbing the electromagnetic radiation generated by the radiation source to generate energy by non-radiative decay. It is this non-radiative decay which is transduced into an electrical signal by the transducer.

The label may therefore be composed of any material which is capable of interacting with the electromagnetic radiation in this manner. Preferably the label is selected from, but not limited to, a carbon particle, a coloured-polymer particle (e.g. coloured latex), a dye molecule, an enzyme, a fluorescent molecule, a metal (e.g. gold) particle, a haemoglobin molecule, a red blood cell, a magnetic particle, a nanoparticle having a non-conducting core material and at least one metal shell layer, a particle composed of polypyrrole or a derivative thereof, and combinations thereof. Preferably, the label is a carbon particle or a gold particle and most preferably a carbon particle.

In the case of a magnetic particle, the electromagnetic radiation is radio frequency radiation. All of the other labels mentioned hereinabove employ light, which can include IR or UV radiation. Gold particles are commercially available or may be prepared using known methods (see for example G. Frens, Nature, 241, 20-22 (1973)). For a more detailed explanation of the nanoparticle label see U.S. Pat. No. 6,344,272 and WO 2007/141581.

Preferably, the present invention uses a particle having a particle size of 20 to 1,000 nm, more preferably 100 to 500 nm. By particle size is meant the diameter of the particle at its widest point. The density of the particle will depend on the type of assay. Where the assay is diffusion-controlled, the particle preferably has a density of 0.5 to 3.0 g/mL, more preferably 1.5-2.0 g/mL and most preferably 1.8 g/mL. In this assay type, the particle is a carbon particle having the aforementioned particle size and density. Where the assay is gravity-assisted, the particle preferably has a density of 1.5 to 23 g/mL, more preferably 15-20 g/mL and most preferably 19 g/mL. In this assay type, the particle is a gold particle having the aforementioned particle size and density.

The label is proximal to the transducer when the binding event has occurred. That is, the label is sufficiently close to the surface of the transducer for the transducer to be able to detect the energy generated by the label on irradiation of the sample. The actual distance between the label and the surface of the transducer will, however, depend on a number of variables, such as the size and nature of the label, the size and nature of the antibodies and the analyte, the nature of the sample medium, and the nature of the electromagnetic radiation and the corresponding settings of the detector. The device of the present invention may include a radiation source which is adapted to generate a series of pulses of electromagnetic radiation and the detector is adapted to determine the time delay between each pulse of electromagnetic radiation from the radiation source and the generation of the electric signal thereby allowing a precise determination of the position of the label with respect to the transducer as discussed with reference to FIG. 1.

The nature of the first, second and third reagents, as well as the labelled reagent, will depend on the nature of the analyte, but they are preferably antibodies. In a particularly preferred embodiment, the labelled reagent comprises an antibody raised to the analyte or the complex or derivative of the analyte, the first reagent is an antibody raised to the analyte or the complex or derivative of the analyte, the second reagent is an isotype control antibody, and the third reagent is an anti-species antibody. In principle, a single molecule could be used for each reagent, but in practice, the first, second and third reagents, as well as the labelled reagent, are a population of molecules. The term “antibody” preferably includes within its scope a Fab fragment, a single-chain variable fragment (scFv), and a recombinant binding fragment.

In a preferred embodiment, particularly but not limited to where the reagents are antibodies, the affinity constant of the third reagent is ≧10⁷ dm³ mol⁻¹, more preferably ≧10⁸ dm³ mol⁻¹. The affinity may be determined using the Scatchard equation with the absorbance measured in an ELISA, a common method for determining antibody affinities, as described in “Immunoassays” Ed. J. P. Gosling, Oxford University Press, 2000, pages 80-83. The second reagent preferably has an affinity such that the kinetic binding rate is ≦10% of the third reagent and more preferably ≦5%.

As alternatives to antibody-antigen reactions, the reagents and analyte may be a first and second nucleic acid where the first and second nucleic acids are complementary, or a reagent containing avidin or derivatives thereof and an analyte containing biotin or derivatives thereof, or vice versa. The reagents may also be aptamers. The system is also not limited to biological assays and may be applied, for example, to the detection of heavy metals in water. The system also need not be limited to liquids and any fluid system may be used, e.g. the detection of enzymes, cells and viruses etc. in the air.

The maximum observable signal is the maximum signal that can be achieved when monitoring the label binding to a surface. In the absence of alternative mass transport phenomena (e.g. convection, magnetic movement, buoyancy, sedimentation, etc.), the binding of particles to the transducer is governed by the diffusion rate of the analyte and labelled reagent which is, in turn, governed largely by the hydrodynamic radius of these components and the viscosity/temperature of the sample. The negative and positive controls should give signals that are independent of the absence or presence of the analyte to be measured.

It has been found that for immunometric (i.e. sandwich or reagent-excess) assays, improvements in performance can be achieved by using an anti-species antibody as the positive control (that recognises an anti-analyte antibody on the labelled reagent), and a non-reactive isotype control antibody (or simply a non-reactive surface) as the negative control. When used in combination, these controls define the upper and lower limits of the measuring range of the system. Thus, the output from the system is defined as the ratio of where the measurement lies between these two limits. Surprisingly this combination can be used to account for variations in the system components (e.g. the material forming the transducer), the environmental conditions, the sample variability and unwanted particle movement (e.g. sedimentation) in combination. The controls provided by the present invention have been found to compensate for all these parameters at the same time.

If a molecule is sufficiently small that formation of an antibody sandwich is not achievable, different types of assay need to be considered. One class of assay for small molecules is the “competitive assay”, in which the analyte of interest competes with another component in the system to prevent binding. In competitive assays the signal is inversely related to the analyte concentration. One particular type of assay is presented in which an antibody to the analyte is immobilised on the transducer, and a labelled analogue of the analyte is introduced into the sample. The analyte and labelled analogue of the analyte then “compete” for the antibody on the surface. In the absence of analyte, then the labelled analogue will bind at the maximum possible rate. However, in the presence of analyte, the antibody on the transducer becomes populated with analyte and the rate of binding of the analogue is diminished. The present invention has applicability to such assays in which the controls reduce variability in the system.

Incorporation of the analogue of the analyte onto the particle can be achieved by first attaching the analogue to a carrier to form an analogue-carrier conjugate, and then attaching the conjugate to the surface of the label. The carrier is preferably a protein, a polysaccharide or a synthetic polymer. The attachment of the analogue to the carrier is preferably by covalent bonding. The attachment of the conjugate to the surface of the carrier is preferably achieved by adsorbing the conjugate to the surface of the label. One approach to mimic maximum binding rate is to use a third reagent on the transducer surface which recognises the carrier, e.g. an antibody raised to the carrier protein. However, the rate of binding in this control may be suboptimal, because the analogue can mask the surface of the carrier, making it sterically hindered. The relative populations of carrier and analogue on the particle could also be quite different.

Thus, for competitive assays, the labelled reagent preferably comprises a label having a carrier attached thereto, wherein the carrier has two different molecules attached thereto. The first molecule is an analogue of the analyte and the second molecule is unrelated, but of similar size to the analogue/analyte. The two different molecules would preferably be conjugated to the carrier in a 1:1 molar ratio to each other. The third reagent would then bind the labelled reagent at a similar rate to the second reagent in the absence of analyte.

The labelled reagent for use in such an assay (i.e. a competitive assay) has been specifically designed for use with the device of the present invention. Thus, the present invention further provides a labelled reagent comprising a label capable of absorbing electromagnetic radiation to generate energy by non-radiative decay, a carrier attached to the label, and attached to the carrier, a first member of a first complementary binding pair and a first member of a second complementary binding pair. The first member of the first complementary binding pair is an analogue of the analyte to be detected and hence the second member of the first complementary binding pair will be the first reagent, for example, an antibody raised to the analyte. The first member of the second complementary binding pair is a molecule which is not normally found in the sample, and which is capable of binding to the third reagent. The second member of the second complementary binding pair will be the third reagent. The carrier is preferably a protein. The first and second complementary binding pairs are different, in the sense that the first and second members of the respective pairs would not have any affinity for one another. By way of an example, the analyte is the drug digoxin, the label is a carbon particle, the carrier is bovine serum albumin, the first member of the first complementary binding pair is digoxigenin (an analogue of digoxin), the second member of the first complementary binding pair is an anti-digoxin antibody, the first member of the second complementary binding pair is fluorescein isothiocyanate and the second member of the second complementary binding pair is an anti-fluorescein antibody.

Examples of the first member of the first complementary binding pair are therapeutic drugs (e.g. carbamazepine, cyclosporine, digoxin, theophylline and gentamycin), drugs of abuse (e.g. opiates, cocaine and amphetamine), vitamins (e.g. vitamin D, vitamin B12 and folate) and hormones (T3, T4, cortisol, progesterone, estradiol and testosterone); and examples of the first member of the second complementary binding pair are BODIPY FL, Dansyl, AlexaFluor 405, AlexaFluor 488, Lucifer Yellow, Rhodamine, Texas Red, biotin (unless used for immobilisation of the first, second and/or third reagents) and dinitrophenyl aminohexanoic acid.

In order to increase the dynamic range of an assay performed in accordance with the present invention, whilst also improving precision, it is preferred to have the first reagent in a plurality of locations on the transducer. These locations may be tuned to different sensitivities, by varying the concentration of the first reagent at each location. Each location may also have its own second and third reagents to act as controls for the different dynamic ranges. This is particularly applicable to competitive assays which are particularly sensitive to the concentration of each of the individual components which make up the system.

The device may also have a plurality of locations as described hereinabove, and the labelled reagent also has two different binding sites. In this instance the analyte blocks one site on the label in one location, but this does not inhibit binding to the reagent in the control.

The analyte may be a macromolecule or a small molecule. The macromolecule is typically a protein, such as a protein-based hormone, and may also be part of a larger particle, such as a virus, a bacterium, a cell (e.g. a red blood cell) or a prion. The small molecule may be a drug.

The term “small molecule” used herein is a term of the art and is used to distinguish the molecule from macromolecules such as proteins and nucleic acids. A small molecule is often referred to in the field of immunoassays as a “hapten”, being a small molecule which, when attached to a large carrier molecule such as a protein, can elicit an immune response and includes molecules such as hormones and synthetic drugs. A small molecule of this type will typically have a molecular weight of 2,000 or less, often 1,000 or less and even 500 or less. The first reagent may be adapted to bind to the analyte itself, although the analyte can undergo a chemical reaction or initial complexing event before binding to the first reagent. For example, the analyte might be protonated/deprotonated in the pH of the assay conditions. Thus, the analyte which is bound to the first reagent may be analyte itself or a derivative of the analyte; both are included within the scope of the present invention.

In a preferred embodiment, the present invention may be used to detect the presence of a small molecule and a macromolecule in the same sample at the same time. That is, the sample includes at least two analytes, one being a small molecule and one being a macromolecule. At least two first reagents are used, one to bind to the small molecule in a competitive assay and one to bind to the macromolecule in an immunometric assay. The second and third reagents are preferably the same, i.e. the positive and negative controls are the same for both assay types.

The sample which is suspected of containing the analyte of interest will generally be a fluid sample, e.g. a liquid sample, and usually a biological sample, such as a bodily fluid, e.g. blood, plasma, saliva, serum or urine. The sample may contain suspended particles and may even be whole blood. An advantage of the method of the present invention is that the assay may be performed on a sample which does contain suspended particles without unduly influencing the results of the assay. The sample will typically be in the order of microlitres (e.g. 1-100 μL, preferably 1-10 μL). In order to hold a fluid sample, the transducer is preferably located in a sample chamber having one or more side walls, an upper surface and a lower surface. Accordingly, the device of the present invention preferably further comprises a chamber for holding a liquid sample containing the analyte or the complex or derivative of the analyte in contact with the transducer. In a preferred embodiment, the transducer is integral with the chamber, i.e. it forms one of the side walls, or upper or lower surface which define the chamber. Preferably the transducer forms the upper surface as shown in FIG. 3. Clearly, the first, second and third reagents and the labelled reagent will be on the interior surfaces of the chamber to allow contact with the sample. The sample may simply be retained by surface tension forces, for example, inside a capillary channel.

The device preferably contains a first chamber containing the first reagent, a second chamber containing the second reagent and a third chamber containing the third reagent. The first, second and third chambers are preferably in fluid communication. The device preferably further contains a capillary channel having a sample receiving end which is contact with the outside of the device and a sample delivery end which is in fluid communication with the sample chamber(s), as shown in the core 21 in FIG. 3.

The labelled reagent and optionally one or more additional reagents are preferably stored in a chamber incorporated into the device of the present invention. The labelled reagent may also be supplied as part of kit incorporating the device and the labelled reagent. Accordingly, the present invention also provides a kit comprising the device as described herein and the labelled reagent. The labelled reagent may be deposited onto the surface of the transducer.

The device of the present invention is not restricted to detecting only one analyte and different analytes may be detected by employing different first reagents which selectively bind each analyte, or a derivative or complex of the analyte, being detected. Multiple tests can be carried out using only one electrical connection to the transducer, by illuminating different locations of the transducer sequentially and interrogating the outputs sequentially.

A potential additional source of background interference is the settling of suspended particles on to the surface of the piezo/pyroelectric transducer, including labelled reagent and cellular components of the sample. This source of interference may be reduced by positioning the transducer above the bulk solution, e.g. on the upper surface of the reaction chamber. Thus, if any settling occurs, it will not interfere with the transducer. Alternatively, the particles could be less dense than the medium and hence float to the surface of the bulk solution rather than settling on the surface of the transducer. This and other modifications are included in the scope of the present invention.

In a preferred embodiment, the device of the present invention consists essentially of the above-described features. By “essentially” is meant that no other features are required to perform the assay. The device may take the form of a separate reader and cartridge, or an integrated device. In the former, the device is formed of a reader and a cartridge, in which the cartridge is releasably engageable with the reader, and in which the reader incorporates the radiation source and the detector, and the cartridge incorporates the transducer and the first, second and third reagents. The reader is preferably a portable reader. The present invention also provides the cartridge comprising the transducer and the first, second and third reagents as defined herein. The cartridge is preferably a disposable cartridge.

The present invention will now be described with reference to the following examples which are not intended to be limiting.

EXAMPLES Example 1 PVDF Film

A poled piezo/pyroelectric polyvinylidene fluoride (PVDF) bimorph film, coated in indium tin oxide was used as the sensing device in the following examples. The indium tin oxide surface was coated with a layer of parylene (of approximate thickness 1 micron) by a vapour phase gas deposition process. This method involved the sublimation and subsequent pyrolysis of a paracyclophane precursor, followed by a free-radical polymerisation on the surface. See WO 2009/141637 for further details. The resulting film was then coated in polystreptavidin solution (200 μg/mL in PBS-10 mmol/L phosphate buffer containing 2.7 mmol/L KCl, 137 mmol/L NaCl and 0.05% Tween) by incubation at room temperature overnight. Polystreptavidin was prepared as described by Tischer et al (U.S. Pat. No. 5,061,640).

Example 2 Materials

Monoclonal antibodies were raised essentially as described in “Monoclonal Antibodies: Properties, Manufacture and Applications” by J. R. Birch and E. S. Lennox, Wiley-Blackwell, 1995, and biotinylated by methods known in the art. Carbon-labelled reporter conjugates were prepared essentially as described by Van Doom et al. (U.S. Pat. No. 5,641,689).

Example 3 Preparation of the Cartridge

As shown in FIG. 3, a cartridge 14 was fabricated to perform the assay. The cartridge 14 was fabricated from an antibody-coated piezo/pyrofilm 15 supported on a stiffener 16. A pressure sensitive adhesive-coated polyester film 17 die-cut to form three sample chambers 18 was applied to the surface. Provision was made to allow for electrical connections to the top and bottom surfaces of the piezo/pyrofilm 15 in order to detect the charge generated. The cartridge 14 is then formed by sandwiching the above components between a top cover 19, to which a label 20 was applied, and a core 21, seal 22 and bottom cover 23.

Assays were carried out by charging the sample chambers with the sample through the capillary channel in the core 21. The piezo/pyrofilm 15 was irradiated through the holes in the top cover 19 with chopped LED light sequentially with LEDs. For each LED pulse, a voltage is measured across the piezo/pyrofilm 15 using an amplifier and analogue to digital (ADC) converter. The ADC signal is plotted over time.

Example 4 An Immunometric Assay with Controls

Strips of PVDF pyroelectric polymer film were coated in three separate areas with a universal streptavidin coating. The three areas were separated by an adhesive spacer attached to the surface of the sensor, allowing subsequent incubation of different biotinylated antibodies onto each area without cross-contamination of the surfaces. The three surfaces (labelled spot 1, spot 2 and spot 3) were coated with three different antibodies at a concentration of 1 μg/mL for 2 hours, then the surfaces were washed and dried in the presence of sucrose stabiliser.

Spot 1 was coated with a negative control antibody (Abcam, cat. No. AB37358, mouse IgG isotype, biotinylated), spot 2 was coated with a monoclonal anti-TSH antibody and spot 3 was coated with a polyclonal goat anti-mouse antibody which acted as the positive control. Once the strips had been prepared they were assembled into cartridges by removing the release liner from the adhesive spacer and attaching each strip to an injection-moulded piece, the final assembly generating three interconnected chambers. These chambers are discoid, with a diameter of approximately 6 mm and a depth of approximately 200 microns, with an internal volume of around 6 μL. Each cartridge also contained a pre-measured quantity of carbon particles coated in a matching anti-TSH antibody. The carbon particles were dried-down in the cartridge and the cartridge had a mechanism for mixing a liquid sample with these dried reagents to give a homogeneous mixture and then moving that mixture to fill the three chambers as described hereinabove. The final concentration of carbon particles in the sample after mixing was around 0.03%. A range of standards with known concentrations of thyroid stimulating hormone (TSH) in pooled human plasma had been prepared previously and the TSH levels confirmed on a lab analyser. A number (15) of repeat measurements were carried out on each batch of plasma. Each measurement used one of the pre-prepared cartridges; the sample was introduced into the cartridge, then the cartridge was inserted into an instrument designed to measure the electrical output from the pyroelectric film.

The instrument contains a displacement pump that mixes the sample, total volume 30 μL, with the carbon particles and then draws the homogeneous mixture into the chambers. The instrument then illuminates each chamber sequentially over a period of 10 minutes using three high-powered LEDs which pulse on for approximately 10 milliseconds followed by a rest period of 90 milliseconds. The instrument amplifies the electrical output which results from the piezo/pyroelectric sensor upon illumination by the LEDs. The signal is generated by the absorption of light by the carbon particles, followed by the dissipation of heat from the particles into the piezo/pyroelectric sensor. Movement of carbon particles in the chamber, either by direct binding events or unwanted sedimentation effects, led to changes in the electrical output over time. The electrical output was converted into a digital signal and the data were manipulated by an on-board processor to give the output from each chamber as a rate-of-change of signal on an arbitrary digital scale, as shown in FIG. 4.

Approximately 15 repeat measurements were carried out on fresh samples at six different TSH concentrations (0, 1.19, 2.54, 5.24, 10.27 and 24.9 mIU/L), giving approximately 90 independent measurements on 90 cartridges, with three individual outputs from each cartridge. The results are set out in Table 1.

TABLE 1 Individual spot outputs for a TSH immunometric assay Conc'n (mIU/L) Spot 1 Spot 2 Spot 3 0 −430.863 −279.172 5136.154 0 −296.232 −307.677 5159.129 0 −380.79 −300.006 5059.33 0 −425.025 −312.423 5185.2 0 −350.304 −201.163 5710.019 0 −451.426 −393.822 5078.857 0 −318.709 −247.329 5412.108 0 −299.058 −191.774 6147.915 0 −389.291 −288.363 5185.041 0 −310.501 −231.196 5758.596 0 −327.634 −250.329 5383.575 0 −444.138 −401.939 5236.325 0 −187.659 −42.5472 6279.682 0 −372.483 −272.93 5778.189 0 −476.934 −321.148 5225.461 1.19 −201.299 319.0674 6474.52 1.19 −481.461 19.62871 6740.012 1.19 52.09882 444.9094 6247.385 1.19 −53.6086 368.0161 6393.713 1.19 −208.354 298.7357 6489.471 1.19 −308.557 153.4231 6519.541 1.19 −421.218 26.96297 6350.21 1.19 −397.324 60.92422 5678.382 1.19 −209.928 296.8847 6632.587 1.19 −490.974 118.0116 6837.468 1.19 −96.5631 384.0316 6567.408 1.19 80.95813 518.0436 7282.508 2.54 −188.86 604.9265 6593.611 2.54 −185.094 712.4469 6208.82 2.54 −76.4958 769.7206 6393.329 2.54 −175.388 707.2111 5886.147 2.54 −510.367 479.456 6125.135 2.54 −378.367 535.6407 5848.956 2.54 −265.587 539.303 6027.396 2.54 −93.8712 864.2397 7658.574 2.54 −272.236 614.9602 6126.295 2.54 −188.466 497.0843 6108.217 2.54 −369.535 535.506 5996.976 2.54 −667.347 243.174 6624.185 2.54 −102.437 873.7737 6793.541 2.54 −2.66799 972.6595 6854.81 5.24 −361.523 1214.043 6143.862 5.24 −256.606 1292.465 7382.176 5.24 −293.167 1405.229 6389.369 5.24 −444.116 1205.073 5563.494 5.24 −223.645 1366.035 6994.522 5.24 395.689 2030.376 7792.629 5.24 −140.611 1260.19 7006.528 5.24 −556.551 1173.356 6982.299 5.24 −503.66 1115.905 5657.636 5.24 −334.672 1136.085 6463.521 5.24 −266.012 1116.454 5936.568 5.24 −736.863 917.7635 7117.094 5.24 −322.266 1447.608 6757.25 5.24 −360.08 1224.651 6324.574 5.24 4.649984 1650.931 6305.24 10.27 −388.176 2481.799 6262.157 10.27 −254.328 2468.424 7132.248 10.27 −340.157 2810.874 6898.286 10.27 −122.522 2352.549 6612.683 10.27 525.3487 3602.455 7480.42 10.27 −8.61887 2605.52 6656.873 10.27 −169.62 2891.513 6812.896 10.27 −96.4464 3015.453 6644.907 10.27 −424.326 2359.531 6447.036 10.27 −284.951 2364.508 6354.903 10.27 −82.7793 2763.07 7170.986 10.27 −144.016 2706.903 6631.797 10.27 −282.749 2311.535 6301.425 10.27 −267.324 3138.583 6741.278 10.27 −334.896 2456.141 5712.895 24.9 −69.9036 4419.074 6317.318 24.9 −55.5322 4513.409 6582.04 24.9 −170.798 4718.44 6472.349 24.9 −135.12 5067.31 6306.789 24.9 −97.5404 4741.483 6936.42 24.9 −291.587 4297.627 6426.706 24.9 −220.074 4174.713 6430.509 24.9 −83.8839 5296.298 7413.253 24.9 −227.478 4265.226 6072.64 24.9 −107.843 5074.911 7078.268 24.9 −30.7539 4531.776 6582.249 24.9 187.5346 4842.325 6938.801 24.9 100.3582 5020.915 6818.821 24.9 −160.695 4690.446 7000.276 24.9 543.4999 5328.066 6631.408

The data from Table 1 were manipulated in one of four ways for every cartridge.

Analysis method 1: For each TSH concentration, the output from spot 2 was averaged, and the mean, standard deviation and coefficient of variation (CV) were calculated at each concentration.

Analysis method 2: For each TSH concentration, the output from spot 1 was subtracted from the output in spot 2 (i.e. spot 1 was used as a baseline for the measurement), then the outputs were averaged, and the mean standard deviation and CV were calculated at each concentration.

Analysis method 3: For each TSH concentration, the output from spot 2 was divided by the output from spot 3 (i.e. spot 3 was used as a scaling factor for the measurement), then the mean, SD and CV were calculated at each concentration.

Analysis method 4: For each TSH concentration, the output from spot 1 was subtracted from the outputs in both spot 2 and spot 3 (i.e. both measurements were baseline corrected). Then the baseline corrected measurement in spot 2 was divided by the baseline corrected measurement in spot 3. The mean, SD and CV was then calculated at each concentration.

The CV values, which are a measure of the assay precision, for each of the four data analysis methods are summarised in Table 2.

TABLE 2 Precision measurements for the data analysis in an immunometric assay. Analyte CV CV concentration No Spot 1 Spot 3 Both (mIU/L) controls control control controls 0 — — — — 1.19 67.64 11.75 66.19 9.30 2.54 30.19 9.31 26.50 9.04 5.24 20.23 6.93 17.17 5.97 10.27 13.43 8.77 10.15 8.37 24.9 7.79 6.11 6.26 5.63

It can be clearly seen from Table 2 that the method using both controls gives the lowest CVs at all concentrations. The dose-response curve for the data without using the controls is shown in FIG. 5, and the similar curve using both controls is shown in FIG. 6.

Example 5 A Competitive Assay with Controls

Cartridges were prepared in a similar manner to Example 4, with the same antibody coated in spot 1. Spot 2 was coated in a monoclonal anti-digoxin antibody and spot 3 was coated in a monoclonal anti-fluorescein antibody. In this example the carbon particles were coated in bovine serum albumin (BSA) which had been pre-treated sequentially with digoxigenin N-hydroxysuccinimide and fluorescein isothiocyanate, both at a five-fold molar ratio with respect to the BSA. The BSA-digoxigenin-fluorescein co-conjugate was coated onto the carbon particles by passive adsorption. Digoxigenin is an analogue of digoxin (a cardiac drug), and also binds to the anti-digoxin antibody, although with a lower binding constant than digoxin itself.

Assays were carried out for digoxin levels in pooled plasma that had been previously spiked with digoxin, the levels of which were confirmed on a laboratory analyser. The presence of digoxin in the sample perturbed the binding of the carbon particles to the anti-digoxin antibody in spot 2 of the cartridge. However, digoxin did not interfere with the binding of particles in spot 3 (note that fluorescein is not normally present in human blood samples). Thus spot 3 acted as a control which was independent of the digoxin concentration.

The data from each spot at different digoxin concentrations are given in Table 3.

TABLE 3 Individual spot outputs for a digoxin competitive assay. Digoxin concentration (ng/mL) Spot 1 Spot 2 Spot 3 0 −102.874 1844.799 3147.182 0 −99.816 1869.622 3212.036 0 −78.5547 2070.562 3573.290 0 −50.2311 1887.335 3278.480 0 −142.978 1944.553 3460.877 0 −8.78611 2034.704 3254.373 0 −77.914 1870.201 3145.893 0 −72.6845 1726.972 2991.395 0 −101.010 1670.998 2997.364 0 −131.198 1945.936 3252.535 1 −124.4 1003.399 3088.815 1 −91.8898 1041.466 2867.851 1 −134.676 949.030 2999.202 1 −111.209 1193.582 3435.829 1 −141.90 947.375 2856.940 1 −67.0826 893.142 2743.814 1 −142.696 830.243 2655.475 1 −127.007 1057.096 3066.226 1 −185.634 874.879 2455.256 1 −134.237 1056.875 3218.095 2 −113.134 637.866 3059.223 2 −113.204 526.357 2544.044 2 −95.2290 577.691 2805.049 2 −129.459 449.852 2713.950 2 −111.356 486.723 2709.436 2 −130.665 780.706 3213.256 2 −143.007 654.540 2829.456 2 −114.48 652.834 2985.415 2 −84.9757 551.450 2523.342 2 −90.4291 538.168 2305.948 4 −86.9180 248.068 2707.177 4 −147.824 273.873 2824.922 4 −117.217 287.317 2566.885 4 −124.834 413.651 3144.755 4 −53.6179 199.637 2427.738 4 −90.009 325.360 2903.013 4 −24.9996 383.641 2784.562 4 −98.0232 249.801 2565.939 4 −134.032 150.454 2402.826 4 −157.303 118.269 2259.995

The data were analysed by the same methods described in Example 4, i.e. without controls, just using control 1, just using control 3, or using both controls. Note that spot 3 was designated the positive control in Example 4, because it mimics the expected response when the system is saturated with analyte. In a competitive assay the dose-response curve is inversely proportional to analyte, so the control in spot 3 mimics the response when there is no analyte present.

It is clearly observed that the precision in the measurement process is much improved by using both controls, as summarised in Table 4.

TABLE 4 Precision measurements for the data analysis methods in a competitive assay. CV Analyte No Spot 1 Spot 3 Both conc. controls control control controls 0 ng/ml 6.53 6.15 3.30 2.79 1 ng/ml 10.94 9.28 5.06 5.16 2 ng/ml 16.62 15.07 11.30 9.30 4 ng/ml 35.53 23.47 27.99 14.96

The dose-response graphs with 1 standard deviation error bars for the assay without controls and with both controls are shown in FIGS. 7 and 8, respectively.

Example 6 Increased Dynamic Range Achieved by Use of Multiple Measurement Surfaces in Combination with Controls

Cartridges were prepared as in Example 5, except that four measurement areas were coated, rather than three. Spots 1 and 4 were the same controls as in Example 5, and spots 2 and 3 were both coated in anti-digoxin antibody, with spot 2 coated in antibody at a concentration of 0.5 μg/mL and spot 3 coated in antibody at 2 μg/mL. Assays for were then run in samples of pooled human plasma which had been spiked with digoxin at a range of concentrations. The data are presented in FIG. 9, showing the mean instrument signal that is observed, along with 1 SD error bars for repeat measurements. The data for spot 2 (0.5 μg/mL anti-digoxin coating) were analysed in conjunction with the two control spots (spots 1 and 4) and the data for spot 3 (1.0 μg/mL anti-digoxin coating) were analysed in conjunction with the two controls (spots 1 and 4) in each cartridge. The methodology of using the control spots was the same as in the Examples 4 and 5 hereinabove, i.e. the output is the baseline-corrected signal in the measurement spot divided by the baseline-corrected signal in the maximum-binding control spot (spot 4 in this instance).

The data are shown in FIG. 9, and it can be clearly observed that the dose-response curve is markedly different for the two anti-digoxin antibody concentrations. For the 0.5 μg/mL coating, the surface becomes saturated with digoxin at lower concentrations, thus the dose response curve is steeper at lower concentrations, giving improved measurements. However, discrimination is lost at concentrations above approximately 15 ng/mL. For the 2 μg/mL coating, the dose-response curve is less steep, so the discrimination is not as good at the low concentrations, but the assay still gives good discrimination at higher concentrations, up to 40 ng/mL. Thus, this assay with controls has the benefit of improved dynamic range over conventional competitive assays.

Example 7 Assay with Controls Across Different Sample Types

A further 100 cartridges were prepared as in Example 4, for the measurement of TSH. These were used as in Example 4, but to measure the TSH levels from approximately 75 healthy human donors. The measurements in this instance were carried out in unseparated whole blood which had been treated with heparin to prevent coagulation of the sample. In parallel, plasma samples were taken from the same donors and these were analysed on a validated laboratory analyser to ascertain the levels of plasma TSH in those donors. The whole blood measurements carried out in the pyroelectric sensor system were manipulated in the same manner as in Example 4, i.e. the outputs were calculated using spot 2, a combination of spots 1 and 2, a combination of spots 2 and 3, or a combination of spots 1, 2 and 3. Since the kinetic measurement was made by diffusion from the plasma component of the whole blood, the output from the instrument was the plasma concentration of the analyte and is independent of the hematocrit of the blood sample.

The measurements according to the four data manipulation methods are shown as scatter plots against the hospital-reported concentrations in FIGS. 10-13. Only data from spot 2 were used in FIG. 10. Data from spot 2 baseline corrected to spot 1 were used in FIG. 11. Data from spot 2 divided by spot 3 were used in FIG. 12. Data from spot 2 baselined to spot 1 expressed as a ratio relative to spot 3 baselined to spot 1 is shown in FIG. 13. The correlation coefficients (R²) for these four methods were 0.42, 0.85, 0.25 and 0.88, respectively, showing that the data manipulation using both controls gave the best correlation with the hospital-measured result.

Examples 4-6 set out hereinabove all show the benefit of improved precision using controls when the sample matrix is a pooled human serum. The improvements must therefore be due to compensating for variability in the cartridge components, instrumentation, environmental conditions and the like, but not due to variability in the sample type. It is well known that human blood and plasma samples are variable in terms of viscosity, hematocrit, interfering factors and general composition. Example 7 shows the benefit of using two controls in improving the accuracy of measurements made across a patient population.

Example 8 Repeat Using Plasma

The same patient samples used in Example 7 were spun down to separate the red cells from the plasma, then the TSH measurement was carried out on the plasma fraction exactly as described in Example 7. The outputs were manipulated exactly as in Example 7, then correlated against the hospital plasma values. The correlation coefficients for spot 2, baselined spot 2, scaled spot 2 and both baselined and scaled spot 2 were 0.61, 0.76, 0.62 and 0.79, respectively.

Examples 7 and 8 indicate that the methodology of using both controls can compensate for variations between different sample types, in additions to other factors such as the components used in the cartridges and/or environmental factors during the measurement.

Examples 4-8 use a similar methodology to provide improved precision and accuracy in either an immunometric or a competitive assay system. There are occasions when it would be beneficial to measure both a small molecule and a large molecule simultaneously in the same sample. For example, one may wish to monitor the plasma concentration of a small molecule drug to ensure that it is in the correct therapeutic range and also measure a protein or hormone to measure the effectiveness of the drug. It would be beneficial to be able to use the same controls for each assay at the same time, in order to limit the amount of sample that is taken or to avoid the necessity of running multiple test in series, rather than in parallel. The following example demonstrates the use of 2 controls which simultaneously improve the performance of a competitive assay and an immunometric assay.

Example 9 Two Assays, One Competitive, the Other Immunometric, Run Simultaneously Using the Same Controls

Cartridges were prepared essentially as described in Examples 4-8. These had six individual sensor surfaces which had been coated with a universal streptavidin surface. Spot 1 was then coated with a biotinylated negative control antibody, spot 6 was coated with a goat anti-mouse antibody, spots 2 and 3 were coated with a monoclonal mouse anti-TSH antibody and spots 4 and 5 were coated with a biotinylated digoxigenin molecule. Although there were six areas in this example, the surface areas of each spot were reduced in these cartridges such that the total sample volume remained at 30 μL, a volume that may be obtained from a finger-prick of blood. Spots 2/3 and 4/5 gave repeat measurements of TSH and digoxin, respectively, in this example, although this was not a specific requirement for the assay to function. It should be noted that the format for digoxin measurements in this example was reversed from that presented in Examples 5 and 6, in that the digoxin analogue was bound to the sensor surface and the anti-digoxin antibody was bound to the carbon particles. However, the principle remains the same and the assay could be carried out in either configuration.

A range of pooled plasma standards spiked with known concentrations of solely TSH, solely digoxin or both TSH and digoxin at known concentrations had been prepared previously and the concentrations confirmed on a lab analyser. Separate determinations for TSH and digoxin had to be carried out for each sample on the lab analyser. Repeat (n=10) assays were carried out on each different sample using cartridges that had been prepared with equal concentrations of carbon particles coated with either anti-TSH antibody or anti-digoxin antibody, although it is also possible to co-coat the two antibodies simultaneously onto the same set of particles.

The instrument output was analysed essentially as described in Examples 4 and 5. For TSH, the output from spots 2 and 3 was averaged, and then the data were manipulated using the two control measurements from spots 1 and 6. Spots 4 and 5 were not used. The four analysis methods were the same as described in Example 4. For digoxin, the output from spots 4 and 5 was averaged, and then the data were also manipulated using the same controls measurements from spots 1 and 6. Spots 2 and 3 were not used. The four analysis methods were the same as described in Example 5.

The precision in each repeat measurement using the four data analysis methods is shown in Table 5. It can be clearly observed that improved precision is achieved in all cases by the use of the two control measurements to define the upper and lower limits of the measurement range.

TABLE 5 Precision measurements for the data analysis methods in a multiplex assay in both immunometric and competitive formats Analyte % CV concentration TSH Digoxin TSH Digoxin No Spot 1 Spot 6 Both No Spot 1 Spot 6 Both (mIU/L) (ng/mL) controls control control controls controls control control controls 0 0 — — — — 4.61 4.58 4.22 3.87 5.58 0 28.87 20.39 24.86 17.04 7.41 6.55 5.12 4.87 0 1 — — — — 7.98 7.36 10.62 6.53 5.58 1 14.11 12.22 13.87 11.64 6.52 5.00 8.06 4.58 2.75 10 27.11 12.42 31.32 11.61 144.41 22.59 140.43 21.74 27 2  6.72  5.75  7.41  4.06 12.82 8.40 9.85 6.81

The instrument outputs (as ratiometric signals, using both controls) are shown in FIG. 14, along with 1 standard deviation error bars. The instrument output for either analyte was independent of the presence or absence of the other.

Example 9 indicates that both controls can be used in parallel to improve the performance of a multiplexed competitive/immunometric assay combination. 

What is claimed is:
 1. A method for detecting an analyte, or a complex or derivative of the analyte, in a sample comprising: exposing the sample to a device, wherein said device comprises; a radiation source adapted to generate a series of pulses of electromagnetic radiation; a transducer having a pyroelectric or piezoelectric element and electrodes which is capable of transducing energy generated by non-radiative decay into an electrical signal; a detector which is capable of detecting the electrical signal generated by the transducer; a first reagent proximal to the transducer, the first reagent having a binding site which is capable of binding a labelled reagent proportionally to the concentration of the analyte in the sample, which labelled reagent being capable of absorbing the electromagnetic radiation generated by the radiation source to generate energy by non-radiative decay; a second reagent proximal to the transducer, the second reagent having a lower affinity for the labelled reagent under the conditions of the assay than the first reagent; a third reagent proximal to the transducer, the third reagent having a binding site which is capable of binding the labelled reagent, wherein the third reagent has an affinity for the labelled reagent which is less influenced than the first reagent by the concentration of the analyte or the complex or derivative of the analyte; and transducing the energy generated into an electrical signal and detecting the signal.
 2. A method as claimed in claim 1, wherein the method is carried out without removing the sample from the transducer between the steps of exposing the sample to the transducer and transducing the energy generated into an electrical signal.
 3. A labelled reagent comprising a label capable of absorbing electromagnetic radiation to generate energy by non-radiative decay, a carrier attached to the label, and attached to the carrier, a first member of a first complementary binding pair and a first member of a second complementary binding pair.
 4. A labelled reagent as claimed in claim 3, wherein the first member of the first complementary binding pair is selected from therapeutic drugs, drugs of abuse, vitamins and hormones, and the first member of the second complementary binding is selected from BODIPY FL, Dansyl, AlexaFiuor 405, AlexaFiuor 488, Lucifer Yellow, Rhodamine, Texas Red, biotin and dinitrophenyl aminohexanoic acid. 